Following literature contributions delineating the deficiencies introduced by the approximations of conventional brachytherapy dosimetry, different model-based dosimetry algorithms have been incorporated into commercial systems for 192 Ir brachytherapy treatment planning. The calculation settings of these algorithms are pre-configured according to criteria established by their developers for optimizing computation speed vs accuracy. Their clinical use is hence straightforward. A basic understanding of these algorithms and their limitations is essential, however, for commissioning; detecting differences from conventional algorithms; explaining their origin; assessing their impact; and maintaining global uniformity of clinical practice.Conventional, Task Group (TG)43-based 1 dosimetry marked an improvement over prior dose calculation formalisms for brachytherapy treatment planning by advocating the use of a source strength quantity traceable to international standards, the introduction of two-dimensional (2D) source anisotropy, and global uniformity in source characterization as well as clinical dosimetry practice. In the past decade, brachytherapy has progressed from the traditional surgical paradigm to modern three-dimensional (3D) image-based treatment planning systems (TPSs) and dose delivery. The information available through patient imaging, however, had not been fully exploited since TG43-based dosimetry relies on sourcespecific data pre-calculated in a standard homogeneous water geometry.1-3 Hence, it disregards patient-specific radiation scatter conditions and the radiological differences of tissue or applicator materials from water.In response to literature on the effect of these shortcomings, which has been reviewed in several recent publications, [4][5][6][7] TPSs have become commercially available that include improved dosimetry algorithms, collectively referred to as model-based dosimetry algorithms (MBDCAs). At the time of writing, these include a deterministic solver of the linear Boltzmann transport equation (LBTE) 8-10 and a collapsed cone superposition (CCS) algorithm 11-17 for 192 Ir high-doserate (HDR) applications.This work reviews the basic features of these algorithms and their clinical implementation and presents illustrative results of their performance. Monte Carlo (MC) simulation is also briefly discussed since, besides being a candidate MBDCA for clinical implementation, it is used for obtaining input data for MBDCAs, as well as for their testing.
DOSIMETRY IN THE BRACHYTHERAPY PHOTON ENERGY RANGEThe vast majority of brachytherapy sources can be considered pure photon emitters.1-3 Figure 1 readily implies that mainly density heterogeneities affect dosimetry of higher photon energy-emitting sources like 192 Ir, since attenuation and energy absorption per unit mass is comparable for all materials except for bone. On the contrary, attenuation and energy absorption differences exist between different tissue compositions for lower photon energies. Literature on the effect...